U.S. patent application number 17/366187 was filed with the patent office on 2022-01-06 for erythrocyte membrane coating.
The applicant listed for this patent is Florida Atlantic University Board of Trustees. Invention is credited to Tanaz ISLAM, Peng YI.
Application Number | 20220000095 17/366187 |
Document ID | / |
Family ID | 1000005763050 |
Filed Date | 2022-01-06 |
United States Patent
Application |
20220000095 |
Kind Code |
A1 |
YI; Peng ; et al. |
January 6, 2022 |
ERYTHROCYTE MEMBRANE COATING
Abstract
A novel erythrocyte (red blood cell) membrane coating derived
from human red blood cells and the methods of preparation and use
thereof are disclosed. The erythrocyte membrane coating may be
developed on a piezoelectric sensor coated with poly-L-lysine.
Inventors: |
YI; Peng; (Boca Raton,
FL) ; ISLAM; Tanaz; (Kelowna, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Florida Atlantic University Board of Trustees |
Boca Raton |
FL |
US |
|
|
Family ID: |
1000005763050 |
Appl. No.: |
17/366187 |
Filed: |
July 2, 2021 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
63047314 |
Jul 2, 2020 |
|
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|
Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A01N 1/0226
20130101 |
International
Class: |
A01N 1/02 20060101
A01N001/02 |
Claims
1. An analytic surface comprising: a supported red blood cell
membrane coating comprising a layer of red blood cell membrane
fragments derived from human red blood cells, wherein said red
blood cell membrane fragments form a continuous layer on a surface
of an analytic substrate.
2. The analytic surface of claim 1, wherein the red blood cell
membrane fragments form a continuous layer on the surface of the
analytic substrate in an aqueous solution.
3. The analytic surface of claim 1, wherein the red blood cell
membrane fragments form a continuous layer on the surface of the
analytic substrate without raising the temperature higher than
about 37.degree. C.
4. The analytic surface of claim 1, wherein the supported red blood
cell membrane coating is formed without a drying process.
5. The analytic surface of claim 1, wherein the supported red blood
cell membrane coating mainly comprises flattened fragments of red
blood cell membranes derived from human red blood cells and
partially comprises aggregates of fragments of red blood cell
membrane fragments derived from human red blood cells.
6. The analytic surface of claim 1, wherein the analytic surface is
negatively charged.
7. The analytic surface of claim 1, wherein the analytic surface is
a piezoelectric sensor.
8. The analytic surface of claim 7, wherein the piezoelectric
sensor is first modified by coating with a positively charged
substance to form a positively charged surface of the piezoelectric
sensor, before deposition of the red blood cell membrane
coating.
9. The analytic surface of claim 7, wherein the piezoelectric
sensor is first modified by coating with poly-L-lysine (PLL).
10. The analytic surface of claim 7, wherein the supported red
blood cell membrane coating is developed on the silica-coated
piezoelectric sensor with a negatively charged surface of a quartz
crystal microbalance with dissipation monitoring (QCM-D)
instrument.
11. The analytic surface of claim 1, wherein the supported red
blood cell membrane is used for toxicity screening for
nanoparticles, nanodrug delivery, or as a biosensor.
12. A method of providing the analytic surface of claim 1, the
method comprising coating the analytic substrate in a suspension of
red blood cell membrane fragments.
13. The method of claim 12, wherein the method is performed at a
temperature not higher than about 37.degree. C.
14. The method of claim 13, wherein the method does not comprise a
drying process.
15. The method of claim 13, wherein the method comprises: selecting
the analytic surface on which to form the supported red blood cell
membrane, wherein the analytic surface is negatively charged;
obtaining a stable baseline by rinsing the analytic substrate with
deionized water at 0.1 mL/min; coating a negatively charged
analytic surface with a cationic layer of a positively charged
substance; and depositing a red blood cell membrane coating,
wherein the red blood cell membrane is comprised of membrane
fragments of human red blood cells.
16. The method of claim 13, wherein the negatively charged analytic
substrate is a piezoelectric sensor with a negatively charged
surface of a quartz crystal microbalance with dissipation
monitoring (QCM-D) instrument.
17. The method of claim 13, wherein the cationic layer of a
positively charged substance is poly-L-lysine.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This non-provisional application claims the benefit under 35
U.S.C. .sctn. 119(e) of U.S. Provisional Application Ser. No.
63/047,314 filed on Jul. 2, 2020 entitled A NOVEL ERYTHROCYTE
MEMBRANE COATING and whose entire disclosure is incorporated by
reference herein.
FIELD OF INVENTION
[0002] This invention relates to an erythrocyte (red blood cell)
membrane coating derived from human red blood cells for use in
various applications, such as a toxicity screening for
nanoparticles, nanodrug delivery, or as a biosensor. It also
relates to the method of forming an erythrocyte membrane coating on
a surface of interest.
BACKGROUND OF THE INVENTION
[0003] The increased use of nanoparticles (NPs) in food additives,
nanodrugs, and cosmetics can cause them to enter human circulatory
system and attach to human cells, particularly red blood cells
(RBCs). Such attachment may lead to cytotoxic effects on RBCs.
Hence, it is critical to investigate the attachment probability of
NPs to RBCs.
[0004] In recent years, significant advancements have been achieved
towards the applications of NPs. NPs have been increasingly used in
the pharmaceutical and biotechnology industries for diagnosis,
imaging, and targeted drug delivery. For example, orally
administered Gastromark.TM. (silicone-coated superparamagnetic iron
oxide NPs), has been used as a contrast agent in gastrointestinal
magnetic resonance imaging (MRI). Ferumoxytol, also known as
Feraheme.TM., (carbohydrate-coated Fe.sub.3O.sub.4 NPs) has been
approved for intravenous administration for the treatment of iron
deficiency anemia for adult patients with chronic kidney disease.
Liposomal nanodrugs like Doxil.RTM. and Onivyde.RTM. are used as
targeted drug delivery for cancer patients. Administration of such
drugs into the human body leads to direct contact of red blood
cells with these NPs.
[0005] Moreover, NPs have been extensively incorporated in various
food products (e.g., food additives) and consumer products such as
food packaging and cosmetics, likely resulting in the entry of NPs
into human digestive systems via different routes. For instance,
titanium dioxide (TiO.sub.2) NPs are commonly used in sunscreens,
dental implants, and food additives for enhancing food color.
[0006] Following entry into the gastrointestinal system, NPs can
penetrate through epithelial and endothelial barriers into the
bloodstream and lymph stream. Additionally, NPs in diesel soot and
carbon black NPs that are released into the air from combustion
engines and power plants can enter human respiratory systems,
translocate from the lung to the circulation system in the human
body, and easily be distributed to lymph nodes, liver, heart,
kidney, and brain.
[0007] The NPs that enter the digestive, respiratory, and
circulatory system would inevitably have contact with and attach to
human cells such as epithelial cells, endothelial cells, and
various blood cells (i.e., red blood cells, white blood cells, and
platelets). Such attachment of nanoparticles to cell membranes has
been proposed to be the initial step for NPs to exert cytotoxic
effects, since it is a critical step toward the disruption of cell
membrane and cellular processes.
[0008] AshaRani et al. shows that attachment of silver NPs (AgNPs)
to lung fibroblast cells induces cell membrane injury and
endocytosis through which AgNPs enter the cells, resulting in the
production of reactive oxygen species (ROS). This further results
in mitochondria damage, deoxyribonucleic acid (DNA) damage and cell
cycle arrest. The attachment of hematite NPs (HemNPs) to human
epithelial cell lines is shown to be a critical step for the uptake
of HemNPs by the cells, which results in loss of membrane integrity
and release of cytokines (i.e., interleukin-6 and interleukin-8)
that are known to promote inflammatory responses.
[0009] It has also been reported that the contact of HemNPs with
myoblast cancer cells form small pores in the membrane through
which NPs enter and damage organelles, triggering cell death and
apoptosis of cells. In addition, adsorption of polystyrene NPs
(PSNPs), commonly used as model plastic NPs, on human intestinal
epithelium cells has resulted in cellular internalization of PSNPs
and partial colocalization of PSNPs in lysosome, raising concerns
on the chronic effects of ingested plastic NPs. In order to
estimate the cytotoxic effects of NPs on human cells, it is crucial
to first measure the probability of NPs attaching to the membranes
of human cells.
[0010] In particular, erythrocytes or red blood cells (RBCs), a
dominant type of blood cell having the highest chance to encounter
the NPs present in the blood stream, is vulnerable to toxicity like
deformation, agglutination and membrane damage when they come to
contact with NPs. For example, attachment of PSNPs to RBCs was
found to increase the osmotic, mechanical and oxidative stress
which resulted in sensitization and cell damage of RBCs.
[0011] Several methodologies have been proposed to utilize RBCs as
drug carriers for the targeted delivery of nanodrugs in the human
body, due to the bioavailability, biocompatibility, and longevity
of RBCs in the circulation system. Brenner et al., use the surface
of RBCs as a hitchhiking tool on which nanocarriers (e.g., nanogel,
liposomes, etc.) are adsorbed and transported to the first organ
downstream of the intravascular injection. In another study,
Doxorubicin loaded poly (lactic-co-glycolic acid) (PLGA) NPs are
hitchhiked onto the surface of RBCs for targeted delivery of the
chemotherapy for lung metastasis treatment. Thus, from both
perspectives of nanoparticle toxicity and nanodrug delivery, it is
important to quantitatively study the attachment of NPs to the
surface of RBCs (i.e., the membrane of RBCs).
[0012] The red blood cell membrane (RBCm), which is derived from
whole red blood cells, is used in a variety of applications. For
example, an electrochemical enzymatic biosensor has been developed
by coating the RBCm on an Au-screen printed electrode for highly
selective glucose measurement. An RBCm coating with multi-lamellar
stacks of human RBC membranes on hydrophilic and hydrophobic silica
chips has also been developed. RBCm was also utilized for blood
group determination using immuno-sensor. Specific binding reagents
for the blood group antigens were immobilized on the piezoelectric
transducer for carrying out an immunological detection method for
the determination of blood group.
[0013] Some prior research works studied the adsorption (or
attachment) of different NPs on the surface of whole RBCs using
various observational tools such as scanning electron microscopy
(SEM), conventional optical microscopy, transmission electron
microscopy (TEM), and confocal laser scanning microscopy (CLSM).
For instance, TEM has been used to locate TiO.sub.2 (.about.20 nm)
aggregates attached on the membrane of and also within RBCs. SEM
has been employed to visualize the distribution of 15 nm TiO.sub.2
over the RBC surface. The attachment of polystyrene NPs (200 nm) to
RBCs has also been observed using SEM after incubation at the
particle/RBC ratio up to 100:1. Nevertheless, quantitative
information on neither the mass deposition nor the probability of
NPs' attachment on the surface (i.e., cell membranes) of real human
cells is still rare due to the lack of appropriate tools.
[0014] Recently, piezoelectric sensors, e.g., quartz crystal
microbalance (QCM) sensors coated with supported lipid bilayer
(SLBs) of synthetic phospholipids such as
palmitoyl-2-oleoyl-snglycero-3-phosphocholine (POPC),
1,2-dioleoyl-sn-glycero-3-phosphocholine (DOPC), etc. have been
used to conduct quantitative studies on interactions between NPs
and model cell membranes. For example, Yi and Chen made DOPC SLBs
on poly-L-lysine (PLL) modified silica-coated QCM crystals for
studying the deposition kinetics of carboxylated multiwalled carbon
nanotubes on model cell membranes. Some recent advancement has been
seen in this field by incorporating sterols, charged lipids such as
phosphatidylinositol, phosphatidylserine, phosphatidylglycerol, and
cell penetrating peptides in SLBs. Moreover, Melby et al. formed a
lipid raft system incorporating highly ordered domains of
sphingomyelin and cholesterol in a DOPC SLB. However, such SLBs
still cannot fully replicate the complex characteristics of real
cell membrane of a mammalian cell.
[0015] Some early efforts have been made in fixing real cell
membranes on the surface of substrates (e.g., electrochemical
sensors and silica chips). Himbert et al. developed a highly
oriented, multi-lamellar solid supported RBC membranes on silica
chips to study the molecular structure of RBC membrane. The RBC
vesicles were prepared via hypotonic treatment and sonication and
deposited on functionalized (hydrophilic and hydrophobic) silica
chips and was annealed at 50.degree. C. and a humidity of
95.8.+-.0.5% in a saturated K.sub.2SO.sub.4 solution for 5
days.
[0016] In another study, an RBC membrane layer was used as a
diffusive layer to develop an electrochemical sensor for highly
selective glucose measurement. An enzyme composite was deposited on
Au-screen printed electrode and RBC vesicles were evenly cast on
the modified surface of electrode. The electrode was incubated with
both enzyme composite and the RBC membranes at 50.degree. C. for 50
min in a dry oven to fabricate the sensor.
[0017] However, the aforementioned supported RBCm layers were
formed at a high temperature (i.e., 50.degree. C.). Such a high
temperature can potentially increase the membrane fluidity, and
lead to an irreversible change in membrane elasticity, protein
denaturation and enzyme inactivation. Thus, the original biological
features of RBCm may have been lost in those layers.
[0018] Accordingly, it is desired to provide an RBCm coating that
retains the biological features of the red blood cell membrane.
[0019] All references cited herein are incorporated herein by
reference in their entireties.
BRIEF SUMMARY OF THE INVENTION
[0020] A first aspect of the invention is a supported red blood
cell membrane (SRBCm) that has been developed on piezoelectric
sensor (i.e., QCM crystals) in aqueous solution at room temperature
from human RBCs. It is an unexpected advantage of the present
invention that these developed SRBCms retain the biological
features of real RBCm.
[0021] In certain embodiments, the invention is a coating that may
be formed on any analytic substrate, the coating comprising RBCm
fragments.
[0022] In certain embodiments, the RBCm fragments form a continuous
layer on a surface of the analytic substrate.
[0023] In certain embodiments, the supported RBCm layer is
developed on a silica-coated piezoelectric sensor with negatively
charged surface of a quartz crystal microbalance with dissipation
monitoring (QCM-D) instrument.
[0024] In certain embodiments, the sensor surface is completely
coated with a cationic layer of poly-L-lysine (PLL).
[0025] In certain embodiments, the coating forms on the surface of
the analytic substrate in an aqueous solution.
[0026] In certain embodiments, the coating forms on the surface of
the analytic substrate without raising the temperature higher than
about 37.degree. C.
[0027] In certain embodiments, the coating forms on the surface of
the analytic substrate without a drying process.
[0028] A second aspect of the invention is a method of coating a
surface of an analytic substrate with a coating comprising RBCm
fragments.
[0029] In certain embodiments, the method comprises soaking the
surface of the analytic substrate in a suspension of RBCm fragments
at room temperature.
[0030] In certain embodiments, the method does not comprise a
drying process.
BRIEF DESCRIPTION OF THE DRAWINGS
[0031] The invention will be described in conjunction with the
following drawings, wherein:
[0032] FIG. 1 is a representation of the formation of supported
erythrocyte membrane on a silica-coated piezoelectric sensor.
[0033] FIG. 2 is a graph depicting frequency and dissipation
responses, which were obtained by the QCM-D during the formation
process of supported erythrocyte membrane on PLL-modified silica
sensor at 1 mM NaCl and 0.2 mM NaHCO.sub.3, pH 7.1.
[0034] FIG. 3A is a graph depicting frequency and dissipation
responses during deposition of 5 mg/L PSNPs on supported
RBCm-PLL-modified surface.
[0035] FIG. 3B is a graph depicting frequency and dissipation
responses during deposition of 5 mg/L PSNPs on PLL-modified sensor
surface in a background solution of 1 mM NaCl and 0.2 mM
NaHCO.sub.3. The contrast between no deposition on RBCm and
favorable deposition of PSNPs on PLL proved complete coverage of
supported RBCm on PLL-modified surface.
[0036] FIG. 4A is a 2D AFM image characterization of surface
morphology of a supported RBCm on a silica crystal sensor of QCM-D
in a solution of 1 mM NaCl and 0.2 mM NaHCO.sub.3.
[0037] FIG. 4B is a graph depicting size distribution of surface
aggregates of RBCm on supported RBCm (SRBCm) summarized from 2D AFM
images of supported RBCm.
[0038] FIG. 4C is a 3D AFM image of supported RBCm.
[0039] FIG. 5A is a graph depicting .DELTA.f.sub.(3) and
.DELTA.D.sub.(3) of HemNP deposition on SRBCm when
.alpha..sub.A<0.0002.
[0040] FIG. 5B is a graph depicting .DELTA.f.sub.(3) and
.DELTA.D.sub.(3) of HemNP deposition on SRBCm when .alpha..sub.A
was in the range of 0.074-0.173.
[0041] FIG. 5C is a graph depicting .DELTA.f.sub.(3) and
.DELTA.D.sub.(3) of HemNP deposition on bare silica sensor. All
deposition experiments of HemNPs were conducted at 1 mM NaCl and pH
5.1. The silica surface was rinsed with 1 mM NaCl for the first
phase of the experiment and 8.8 mg/L HemNPs were deposited on
silica surface 1 mM NaCl for the second phase of the
experiment.
[0042] FIG. 5D is a graph depicting deposition attachment
efficiencies (.alpha..sub.D) on SRBCm of 5 mg/L PSNPs at 1 mM NaCl
and 0.2 mM NaHCO.sub.3 and 8.8 mg/L HemNPs at 1 mM NaCl. The error
bar represents the standard deviation from mean .alpha..sub.D.
[0043] FIG. 6 is a graph depicting the entire frequency and
dissipation profiles of the QCM-D experiment of PSNPs deposition on
SRBCm, the deposition stage of which has been shown in FIG. 3a. The
stages are denoted by A to F. A: Stable baselines are obtained by
rinsing silica surface with DI water; B: Formation of PLL coating
on the silica surface; C: Rinsing PLL layer with 1 mM NaCl and 0.2
mM NaHCO.sub.3; D: Formation of SRBCm E: Rinsing SRBCm with 1 mM
NaCl and 0.2 mM NaHCO.sub.3. F: 5 mg/L PSNPs in 1 mM NaCl and 0.2
mM NaHCO.sub.3 was introduced and no deposition take place.
[0044] FIG. 7 is a graph depicting complete frequency and
dissipation profiles during a QCM-D experiment of HemNP deposition
on SRBCm which is a duplicate experiment for the data presented in
FIG. 5B. The stages of the QCM-D experiment are denoted by A to G.
A: Stable baselines are obtained by rinsing silica surface with DI
water; B: Formation of PLL coating on the silica surface; C:
Rinsing PLL layer with 1 mM NaCl and 0.2 mM NaHCO.sub.3; D:
Formation of SRBCm in 1 mM NaCl and 0.2 mM NaHCO.sub.3 ; E: Rinsing
SRBCm with 1 mM NaCl and 0.2 mM NaHCO.sub.3; F: Rinsing SRBCm with
1 mM NaCl; G: 8 mg/L HemNPs in 1 mM NaCl (pH 5.1) was introduced,
and continuous deposition of HemNPs on SRBCm occurred.
.alpha..sub.A of HemNPs was 0.173.
[0045] FIG. 8 is a graph depicting complete profiles of frequency
and dissipation of a QCM-D experiment of HemNP deposition SRBCm
coated sensor. The stages are denoted by A to G. A: Stable
baselines are obtained by rinsing silica surface with DI water; B:
Formation of PLL coating on the silica surface; C: Rinsing PLL
layer with 1 mM NaCl and 0.2 mM NaHCO.sub.3; D: Formation of SRBCm
in 1 mM NaCl and 0.2 mM NaHCO.sub.3; E: Rinsing SRBCm with 1 mM
NaCl and 0.2 mM NaHCO.sub.3; F: Rinsing SRBCm with 1 mM NaCl; G: 8
mg/L HemNPs in 1 mM NaCl (pH 5.1) was introduced, and deposition of
HemNPs on SRBCm occurred. .alpha..sub.A of HemNPs was 0.0002.
[0046] FIG. 9 is a graph depicting aggregation attachment
efficiencies of HemNPs as functions of NaCl concentration at pH
5.1.
DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS OF THE INVENTION
[0047] In certain embodiments, the present invention comprises a
red blood cell membrane (RBCm) coating derived from human red blood
cells (RBCs). The RBCm coating is mainly composed of flattened
fragments of original RBC membranes and partially composed of
aggregates of fragments of RBC membrane derived from human red
blood cells. The RBC membrane derived from human red blood cells is
formed by a single layer of phospholipid bilayers (lipid bilayers)
which is made of two layers of phospholipid molecules integrated
with membrane proteins, cholesterol, and proteins channels. Each
phospholipid molecule has hydrophilic phosphate head, and two
hydrophobic lipid tails. They orient them such that the polar heads
reside on the outer surface while tails remain in the interior of
each layer.
[0048] In certain embodiments, the surface of the original RBC
membrane may include, for example, enzymes, ligands or biomolecules
that bind with a target molecule such as glucose.
[0049] The applications of the supported RBCm coatings of the
invention are varied. The RBCm coating can play a pivotal role in
quantifying the binding of various biomolecules, drugs, or
nanoparticles (NPs) on RBC membrane. For instance, the RBCm coating
can be used to scrutinize the toxicity of nanodrugs, nanocarriers
and nanoparticles on red blood cell. It is crucial to
quantitatively determine the attachment probability of those
nanoparticles on RBCs upon collisions. The more likely the NPs
attach to the RBCm the more likely the NPs can exert toxic effects
on RBCs.
[0050] In certain embodiments, the supported RBCm may be used for
fabricating new biosensors for measuring the binding affinity of
biomolecules (e.g., glucose, insulin, antibodies, proteins, RNA,
etc.), drugs (e.g., penicillin, aspirin, ibuprofen, nicotine,
caffeine, etc.), alcohol, nanoparticles, and ultrafine particulates
found in smoke on red blood cells.
[0051] In certain embodiments, the supported RBCm is formed on the
surface of an analytic surface. For a negatively charged analytic
surface, for example, the negatively charged analytic substrate may
be first modified by coating with a positively charged substance,
such as poly-L-lysine (PLL), to form a positively charged surface
of the analytic substrate, before deposition of the RBCm coating.
Positively charged PLL is a synthetic polymer which adsorbs
electrostatically from the solution onto the negatively charged
surface.
[0052] In certain embodiments, the supported RBCm is developed on a
piezoelectric sensor such as quartz crystal microbalance (QCM) in
aqueous solution at room temperature from human RBCs.
[0053] In certain embodiments, the suspension is formed by well
dispersed RBC membrane, which is prepared from whole blood and
characterized thoroughly using cryogenic transmission electron
microscopy.
[0054] In certain embodiments, the negatively charged surface is
modified with PLL to deposit the RBCm coating on it.
[0055] In certain embodiments, the RBCm coating is formed without a
drying process, such as any process that can result in the exposure
of RBCm coating to the air.
[0056] The invention will be illustrated in more detail with
reference to the following Examples, but it should be understood
that the present invention is not deemed to be limited thereto.
EXAMPLES
Example 1. Materials.
[0057] Preparation and Characterization of Hematite Nanoparticles
(HemNPs) and Carboxylated Polystyrene Nanoparticles (PSNPs). The
4.4 g/L of HemNPs stock suspension was synthesized through the
forced hydrolysis of FeCl.sub.3 and used before in previous
literature by Huynh et al. From their TEM image of HemNPs, it was
found that HemNPs were mostly spherical with some angular feature
and had a size of 87 (avg.) nm. For experiments, 8.8 mg/L HemNPs in
1 mM NaCl was prepared from the stock suspension and then sonicated
using a bath sonicator (Branson M3800, USA) for 60 minutes to break
up aggregates of HemNPs. The carboxylated PSNPs with the nominal
size of 104 nm were purchased from Polysciences, Inc. 5 mg/L PSNPs
in 1 mM NaCl and 0.2 mM NaHCO.sub.3 (pH 7.1) solution was prepared
for experiments and sonicated using the bath sonicator for five
minutes to break up aggregates.
[0058] Reagents and Solution Chemistry. All experiments were
conducted at 25.degree. C., except for the preparation of RBCm
suspension. NaCl and NaHCO.sub.3 electrolyte stock solutions were
prepared using ACS-grade chemicals (VWR, PA). A stock solution of
10 g/L cationic poly-L-lysine (PLL) hydrobromide (P-1274,
Sigma-Aldrich, St. Louis, Mo.) was prepared in HEPES buffer
solution made up of 10 mM N-(2-hydroxyethyl)
piperazine-N'-(2-ethanesulfonic acid) (HEPES) (H4034,
Sigma-Aldrich, St. Louis, Mo.) and 100 mM NaCl. Both HEPES and PLL
(molecular weight of 70,000-150,000) stock solutions were filtered
through 0.2 .mu.m polypropylene syringe filters (VWR, PA). All
experiments with PSNPs were conducted at 1 mM NaCl and pH 7.1
buffered with 0.2 mM NaHCO.sub.3. All experiments with HemNPs were
conducted at 1 mM NaCl and pH 5.10.+-.0.02 (adjusted by 10 .mu.M
HCl). All solutions were prepared with DI water (MilliporeSigma,
MA) with a resistivity of 18.2 MS/cm.
[0059] Preparation of Colloidal Suspension of RBCm Fragments from
Human Blood. The whole blood (blood group of 0 negative) was
purchased from the Continental Blood Bank (Fort Lauderdale, Fla.).
The samples were preserved with dipotassium
ethylenediaminetetraacetic acid (K.sub.2EDTA) to prevent
coagulation of the blood cells. At first, the RBC pellets were
isolated from plasma by centrifuging (centrifuge 40R, Thermo
Scientific, Danville, Ind.) the whole blood at 4.degree. C. and 800
g for 10 min. The resulting precipitates of erythrocytes were
collected and washed three times through centrifugation,
withdrawing supernatants, and refilling with phosphate buffered
saline (PBS) (Amresco Inc., OH) at pH 7.4. Then, 4-time diluted PBS
(0.25.times.PBS) was added to trigger hemolysis of erythrocytes.
The hemolyzed solution was centrifuged at 2500 g and 4.degree. C.
for 10 min to separate the cellular contents (i.e., hemoglobin)
from the RBC membrane. The supernatant was discarded via a
micropipette. The process of refilling with 0.25.times.PBS,
centrifugation, and discarding supernatant was repeated three
times. The resulting ghosts of RBCm was further washed with DI
water three times using the above process. Vortex was used to
redisperse the settled RBC ghosts every time during washing with
either 0.25.times.PB S or DI water.
[0060] After the hypotonic treatment using 0.25.times.PBS, less
than 1 mL of pink RBC ghosts were produced and after DI water
washing RBC ghosts turned white in color. The centrifuge tubes
containing white RBC ghosts in DI water were kept at 3.degree. C.
and allowed for static diffusion for 3 days until the erythrocyte's
membranes spontaneously dispersed into the DI water and formed the
homogenous stock of RBCm suspension. To preserve the RBCm
suspension for longer duration, they were stored at -20.degree. C.
Approximately, 10 ml RBCm suspension was harvested from 6 ml whole
blood resulting in the membrane concentration in RBCm suspension
equal to 60% of that in whole blood. Before use, NaCl and
NaHCO.sub.3 were added to the 10 mL stock RBCm suspension to have 1
mM NaCl and 0.2 mM NaHCO.sub.3 at pH 7.1. Then, the RBCm suspension
was sonicated with probe sonicator (Q55, Qsonica, Newtown, Conn.)
for ten cycles of 10 s sonication to further reduce the size of
RBCm pieces.
[0061] Quartz Crystal Microbalance with Dissipation Monitoring
(QCM-D). The formation of SRBCm and the deposition of NPs on SRBCm
were conducted using a QCM-D (E1, Q-Sense, Vastra Frolunda, Sweden)
with QFM 401 flow module. A 5-MHz AT-cut quartz crystal
silica-coated (QSX 303, Q-Sense) sensor was mounted in the
module.
[0062] In order to conduct deposition experiments and derive the
deposition attachment efficiencies of NPs on SRBCm, a SRBCm was
first developed on the surface of a silica-coated crystal sensor.
In order to acquire the deposition kinetics of PSNPs and HemNPs on
SRBCm in their corresponding electrolyte solution, both deposition
experiments on SRBCm and favorable deposition experiments were
performed.
[0063] For deposition experiments on SRBCm, the crystal surface was
first coated by PLL by successive rinsing of the surface with HEPES
buffer, 0.1 g/L PLL solution, and additional HEPES buffer. During
the PLL adsorption process, there were sharp decrease and increase
of the frequency and dissipation, respectively until they reached a
plateau suggesting the crystal surface is completely coated with
PLL. Then, the PLL layer was covered by RBCm coating. After rinsing
with the corresponding background solution, NP suspension was
introduced into measurement chamber and deposition of NPs on SRBCm
took place. The favorable deposition experiments of cationic HemNPs
were conducted on bare silica surface. The negatively charged
silica surface was rinsed by 1 mM NaCl (pH 5.1) to get good
baselines. Then, the HemNPs suspension was directed across the
silica surface for deposition to occur at 1 mM NaCl and pH 5.1. For
PSNPs, the favorable deposition was conducted on PLL-modified
silica surface at 1 mM NaCl and 0.2 mM NaHCO.sub.3.
[0064] Cryogenic Transmission Electron Microscopy (Cryo-TEM).
Cryo-TEM imaging was employed to examine the RBCm fragments in the
erythrocyte membrane suspension at 1 mM NaCl and 0.2 mM
NaHCO.sub.3. Three microliters of the suspension were applied to
carbon grids (Protochips, Inc., Morrisville, N.C.) and vitrified
using a Vitrobot (Mark IV, FEI Co., Hillsboro, Oreg.) which
operated at 4.degree. C. and .about.90% humidity in the control
chamber. Then, the vitrified sample was stored under liquid
nitrogen and transferred into a cryo-holder (Model 626/70, Gatan,
Inc., Pleasanton, Calif.) for imaging. The sample was inspected
using a camera (4k.times.4k CCD, Gatan, Inc., Pleasanton, Calif.)
on a TEM (Tecnai G2 F20-TWIN, FEI Co., Hillsboro, Oreg.) operated
at a voltage of 200 kV using low dose conditions (.about.20
e/.ANG.2). Images were recorded with a defocus of approximately -3
.mu.m to improve contrast.
[0065] Atomic Force Microscopy (AFM) Imaging. AFM imaging of SRBCm
and bare silica surface were performed using an atomic force
microscope (5420, Agilent Technologies, Inc, Santa Clara, Calif.)
in aqueous solutions (i.e., RBCm suspension for SRBCm or DI water
for silica surface). A cleaned silica quartz crystal sensor was
soaked in 0.1 g/L PLL for 20 min and then subsequently soaked in
RBCm suspension for 30 min to form SRBCm on the PLL-modified sensor
before observation. Bare silica surface was just soaked in DI water
for imaging. The petri dish with the prepared sensor was mounted on
the stage of AFM. Triangular silicon nitride cantilever with a
nominal spring constant of 0.088 N/m (HYDRA4V-100NG, Applied
Nanostructures, Inc., Mountain View, Calif.) was mounted in the AFM
cell. The images were acquired in AC mode with 30% drive, a
scanning speed of 2.02 in/s, and manual tuning. The images were
further processed using Pico image tool.
Example 2: Preparation and Characterization of RBC Membrane
Suspension
[0066] In order to develop a supported RBCm coating on the QCM
sensor, RBCm suspension was first prepared. Erythrocytes were
isolated from plasma and buffy coat after centrifugation of whole
blood, and then washed 3 times by phosphate-buffered saline (PBS)
followed by hemolysis and hypotonic treatment in 4-time diluted
PBS. The remaining RBCm ghosts were sequentially washed by 4-time
diluted PBS and deionized (DI) water before they were stored in DI
water under static condition at 3.degree. C. in the refrigerator
for 3 days. The RBCm ghosts had been fully dispersed into colloidal
fragments after the 3-day static diffusion. Right before use, probe
sonication was applied to further reduce the size of RBCm fragments
and the solution chemistry of the suspension was adjusted to be 1
mM NaCl and 0.2 mM NaHCO.sub.3. The final concentration of RBCm in
the working suspensions was equal to 60% of the RBCm concentration
in the original whole blood. Dispersed RBC membranes in a solution
of 1 mM NaCl and 0.2 mM NaHCO.sub.3 (pH 7.1) after sonication looks
like a translucent colloid suspension. The cryogenic transmission
electron microscopy (cryo-TEM) image of RBCm suspension shows that
erythrocyte membrane had been broken off into colloidal fragments
in the suspension. The fragments were amorphous in size or shape.
Some fragments were overlapped, developing RBCm aggregates. Their
sizes were ca. 450 nm in short diameter and ca. 600 nm in long
diameter. The hydrodynamic diameter of the RBCm colloidal fragments
in the suspension was determined by dynamic light scattering (DLS)
to be 390.+-.90 nm (avg..+-.SD.). The zeta potential of RBCm
fragments was determined to be -0.53.+-.0.41 mV (avg..+-.SD.) in
the solution of 1 mM NaCl and 0.2 mM NaHCO.sub.3, at pH 7.1.
Example 3: Formation of Supported RBCm on a Silica-Coated
Piezoelectric Sensor
[0067] The supported RBCm (SRBCm) layer was developed on a
silica-coated piezoelectric sensor of a quartz crystal microbalance
with dissipation monitoring (QCM-D) instrument. FIG. 2 presents the
representative normalized frequency and dissipation shifts at the
third overtone, denoted as .DELTA.f.sub.(3) (=.DELTA.f.sub.3/3) and
.DELTA.D.sub.(3), respectively, of the sensor during the formation
of the SRBCm. A stable baseline was first obtained by rinsing the
substrate surface with deionized (DI) water at 0.1 mL/min. Then,
the negatively charged sensor surface was completely coated by a
cationic layer of PLL by sequentially introducing ca. 2 mL of HEPES
buffer (i.e., 10 mM N-(2-hydroxyethyl)
piperazine-N'-(2-ethanesulfonic acid) (HEPES) and 100 mM NaCl), ca.
2 mL of 0.1 g/L PLL dissolved in HEPES buffer, and ca. 2 mL of
HEPES buffer across the sensor surface. After obtaining good
baselines of frequency and dissipation by rinsing the PLL-modified
surface with a background electrolyte solution of 1 mM NaCl and 0.2
mM NaHCO.sub.3 at pH 7.1, the RBCm suspension at the same solution
chemistry was introduced into the measurement chamber.
[0068] As shown in FIG. 2, .DELTA.f.sub.(3) decreased and
.DELTA.D.sub.(3) increased sharply due to the deposition of RBCm
fragments on PLL-modified sensor surface. As the colloidal
fragments of RBC membrane and PLL layer carried negative and
positive surface charge, respectively, at pH 7.1, the deposition of
RBCm fragments on the PLL-modified surface was favorable due to
electrostatic attraction. Both frequency and dissipation attained
plateaus in 3 min after starting of the deposition, signifying
that, the surface of sensor had been completely coated with RBCm
fragments and no multilayer deposition took place. Thus, we
speculate that the SRBCm was mainly a single layer of flattened
fragments of RBCm which had complete coverage on the surface of PLL
modified sensor, as illustrated by the cartoon in FIG. 1. Since
RBCm fragments were pieces of original erythrocyte membranes, the
SRBCm should retain the important biological components of cell
membrane i.e., phospholipid bilayer, sterols, proteins, etc.
[0069] The complete coverage of supported RBCm on the PLL-modified
silica-coated piezoelectric sensor was verified through deposition
experiments of carboxylated polystyrene nanoparticles (PSNPs) on
SRBCm.
[0070] A supported erythrocyte membrane was developed first.
Following the good baseline in the background solution (i.e., 1 mM
NaCl and 0.2 mM NaHCO.sub.3), 5 mg/L PSNPs in the same electrolyte
solution was introduced across the supported RBCm. No noticeable
PSNPs deposition were observed. Thus, both RBCm and PSNPs carried
negatively surface charge and the electrostatic repulsion impeded
the deposition of PSNPs on the SRBCm coating. On the contrary, in a
control experiment the PLL layer was not covered by RBCm.
[0071] When 5 mg/L PSNPs in 1 mM NaCl and 0.2 mM NaHCO.sub.3 was
introduced into the measurement chamber, due to electrostatic
attraction PSNPs readily attached to the PLL layer with a favorable
deposition rate of 2.48.+-.0.08 (avg..+-.SD.) Hz/min. The contrast
between FIGS. 3A and 3B indicated that there was a complete
coverage of RBCm on the PLL-coated surface. Even if there was any
pore in the supported RBCm, the diameter of pore should have been
less than the size of PSNPs, i.e., 106 nm.
Example 4: Characterization of Surface Morphology of Supported RBCm
using AFM
[0072] AFM images of the surface morphology of a supported RBCm on
the silica crystal sensor of QCM-D has been obtained in a solution
of 1 mM NaCl and 0.2 mM NaHCO.sub.3. Two-dimensional (2D) and
three-dimensional (3D) images were taken of the surface morphology
of the SRBCm. A control AFM image of bare surface of silica crystal
sensor was obtained in DI water. Most of the SRBCm area had the
height of a few nanometers which is consistent with the thickness
of cell membranes. Thus, consistent with the QCM-D results, the AFM
images also show that SRBCm was mainly consisted of a single layer
of flattened RBCm. There were also aggregates of RBCm fragments
embedded in or deposited on the SRBCm. Some aggregates have the
oval shape and some may have a dumbbell-like shape. The range of
the longest diameter of the RBCm aggregates was from 120 nm to 590
nm which is consistent with the size of RBCm aggregates observed in
cryo-TEM image. The maximum height of aggregates was 53.9 nm.
Imaged SRBCm and aggregates of RBCm were stable upon repeated
imaging and no lateral movement was detected.
[0073] The size distribution of RBCm aggregates shows a mean of the
size distribution of 0.28 .mu.m. The distribution is positively
skewed (skewness=0.82). In other words, the size data of most
membrane fragments are clustered around the left tail of the
distribution.
Example 5: Deposition Kinetics and Attachment Efficiency of
Hematite Nanoparticles on Supported RBCm
[0074] In order to measure the attachment probability of HemNPs
upon collision with the surface of erythrocytes, the deposition
attachment efficiency (.alpha..sub.D) of HemNPs on SRBCm was
derived through QCM-D deposition experiments of HemNPs on both
SRBCm and bare silica surface. The .alpha..sub.D was calculated
using a classic methodology by taking the ratio of shift rate of
frequency during the deposition on the SRBCm to that during the
favorable deposition on silica. The HemNPs were suspended in the
solution of 1 mM NaCl, at pH 5.1.
[0075] A SRBCm was first developed on the PLL-modified silica
surface as described before. Then, the SRBCm was rinsed with the
solutions of 1 mM NaCl and 0.2 mM NaHCO.sub.3 (pH 7.1) and 1 mM
NaCl (pH 5.1), sequentially, until the normalized frequency and
dissipation responses were stabilized. Afterwards, 8.8 mg/L HemNPs
suspended in 1 mM NaCl was introduced into the measurement chamber.
Since RBCm in 1 mM NaCl (pH 5.1) had negative zeta potential
(-0.78.+-.0.73 mV), deposition occurred when the positively charged
HemNPs approached to the negatively charged RBCm surface.
[0076] The deposition of the positively charged HemNPs on
negatively charged silica surface was conducted as favorable
deposition experiments during which the attachment probability of
HemNPs was 100% due to the electrostatic attraction between
particles and surfaces.
[0077] As the deposition of HemNPs proceeded beyond the initial a
few minutes, two types of deposition behavior were observed
depending on the aggregation propensity of HemNPs, which can be
quantified by aggregation attachment efficiency
(.alpha..sub.A).
[0078] Even slight change in the aggregation attachment efficiency
could result in significant difference in the deposition behavior
of HemNPs on SRBCm. When .alpha..sub.A<0.0002, HemNPs had almost
no propensity to attach to each other. HemNPs quickly saturated all
the available sites on SRBCm. It is speculated that HemNPs quickly
saturated and formed a monolayer on the SRBCm at the surface
density of 35.+-.15 ng/cm.sup.2 and no multilayer deposition
occurred since HemNPs could not attach to other HemNPs at such low
.alpha..sub.A. The .alpha..sub.D of HemNPs on SRBCm at 1 mM NaCl
and pH 5.1, was thus determined to be 0.99.+-.0.85
(avg..+-.SD.)
[0079] When .alpha..sub.A was in the range of 0.074 to 0.173,
HemNPs had noticeable propensity to, although still low, to attach
to other HemNPs. Thus, continuous deposition of HemNPs was observed
on SRBCm. The continuous deposition of HemNPs was due to the
multilayer deposition of HemNPs on SRBCm.
Example 6: Deposition Kinetics and Attachment Efficiency of
Carboxylated Polystyrene Nanoparticles on Supported RBCm
[0080] The attachment efficiency of 5 mg/L PSNPs on SRBCm at 1 mM
NaCl and 0.2 mM NaHCO.sub.3, pH 7.1 has been derived using the
methodology similar to that for HemNPs using the data presented in
FIGS. 3A and 3B. As shown by FIG. 3A, no frequency decrease was
observed when 5 mg/L PSNPs flowed across SRBCm indicating no
deposition of PSNPs upon the interactions with SRBCm. FIG. 6
presents the entire frequency and dissipation data for a duplicate
QCM-D experiment which also shows no deposition.
[0081] One of the reasons for no deposition of PSNPs on SRBCm was
the electrostatic repulsion between them. Moreover, as the head
groups of phospholipids are highly hydrophilic, a water layer may
have formed on a SRBCm resulting in repulsive hydration force which
may also deter the direct contact of PSNPs to SRBCm.
[0082] A supported erythrocyte membrane (SRBCm) has been
successfully developed on a piezoelectric sensor in the aqueous
solution at room temperature. Membranes of RBCs were extracted from
whole blood and well dispersed. The dispersed membranes were
characterized through cryogenic transmission electron microscopy
(cryo-TEM), dynamic light scattering, and zeta potential analysis.
The size of the dispersed membrane fragments was 390.+-.90 nm and
their zeta potentials were -0.53.+-.0.41 mV at 1 mM NaCl and 0.2 mM
NaHCO.sub.3, pH 7.1. The immobilization of membranes was achieved
through deposition on the piezoelectric sensor used in a quartz
crystal microbalance with dissipation monitoring (QCM-D) system.
The frequency shift of -26.2.+-.4.1 Hz and the low ratios of
dissipation shift to frequency shift (0.72.+-.0.15.times.10.sup.-7
Hz.sup.-1) suggests the formation of a thin and rigid membrane
layer. The SRBCm is comprised of a monolayer of flattened fragments
of erythrocyte membranes. The complete coverage of the membrane
layer on the sensor was verified through deposition experiments of
polystyrene nanoparticles. The surface morphology of the membrane
coating was characterized via atomic force microscopy. It was found
that aggregates of RBCm with the mean size of 280 nm were present
on SRBCm. The deposition attachment efficiencies of model
nanoparticles, HemNPs and PSNPs, on SRBCms were obtained in the
solution of 1 mM NaCl at pH 5.1 and the solution of 1 mM NaCl and
0.2 mM NaHCO.sub.3, respectively, using a well-established
methodology. While PSNPs did not have any deposition, HemNPs had
the attachment efficiency of 0.99.+-.0.85 (avg..+-.SD.). The HemNPs
with negligible aggregation propensity (.alpha..sub.A<0.0002)
quickly saturated the surface of SRBCm at the surface density of
35.+-.15 ng/cm.sup.2 and no further deposition was observed. In
contrast, the HemNPs with noticeable aggregation propensity
(.alpha..sub.A=0.074 to 0.173) had continuous deposition on SRBCm,
probably due to multilayer deposition.
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